WO1992013025A1 - Adhesifs et agents d'etancheite a base de collagene et leurs procedes de preparation - Google Patents

Adhesifs et agents d'etancheite a base de collagene et leurs procedes de preparation Download PDF

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Publication number
WO1992013025A1
WO1992013025A1 PCT/US1992/000704 US9200704W WO9213025A1 WO 1992013025 A1 WO1992013025 A1 WO 1992013025A1 US 9200704 W US9200704 W US 9200704W WO 9213025 A1 WO9213025 A1 WO 9213025A1
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Prior art keywords
collagen
anhydride
combination
initiator
composition
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Application number
PCT/US1992/000704
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English (en)
Inventor
Charles D. Kelman
Dale P. Devore
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Autogenesis Technologies, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Autogenesis Technologies, Inc. filed Critical Autogenesis Technologies, Inc.
Priority to DE69232835T priority Critical patent/DE69232835D1/de
Priority to EP92907406A priority patent/EP0569551B1/fr
Priority to CA002101637A priority patent/CA2101637C/fr
Publication of WO1992013025A1 publication Critical patent/WO1992013025A1/fr

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Classifications

    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08H—DERIVATIVES OF NATURAL MACROMOLECULAR COMPOUNDS
    • C08H1/00—Macromolecular products derived from proteins
    • C08H1/06—Macromolecular products derived from proteins derived from horn, hoofs, hair, skin or leather
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/10—Polypeptides; Proteins
    • A61L24/102—Collagen
    • C—CHEMISTRY; METALLURGY
    • C09—DYES; PAINTS; POLISHES; NATURAL RESINS; ADHESIVES; COMPOSITIONS NOT OTHERWISE PROVIDED FOR; APPLICATIONS OF MATERIALS NOT OTHERWISE PROVIDED FOR
    • C09J—ADHESIVES; NON-MECHANICAL ASPECTS OF ADHESIVE PROCESSES IN GENERAL; ADHESIVE PROCESSES NOT PROVIDED FOR ELSEWHERE; USE OF MATERIALS AS ADHESIVES
    • C09J189/00—Adhesives based on proteins; Adhesives based on derivatives thereof
    • C09J189/04—Products derived from waste materials, e.g. horn, hoof or hair
    • C09J189/06—Products derived from waste materials, e.g. horn, hoof or hair derived from leather or skin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/0079—Methods or devices for eye surgery using non-laser electromagnetic radiation, e.g. non-coherent light or microwaves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F9/00802—Methods or devices for eye surgery using laser for photoablation
    • A61F9/00817—Beam shaping with masks
    • A61F9/00819—Beam shaping with masks with photoablatable masks

Definitions

  • Collagen the major connective tissue protein in animals, possesses numerous characteristics not seen in syn ⁇ thetic polymers. Characteristics of collagen often cited include good compatibility with living tissue, promotion of cell growth, and absorption and assimilation of implantations (Shimizu, R. et al. Biomat. Med. Dev. Art. Ore... 5(1): 49-66 (1977) ) . Various applications of this material are being tested, for example, as dialysis membranes of artificial kidney (Sterzel, K.H. et al. Ameri. Soc. Artif. Int. Organs 17: 293 (1971)), artificial cornea (Rubin, A.L. et al. Nature 230: 120 (1971) and U.S.
  • Patent 4,581,030 vitreous body (Dunn, M. et al. A er. Soc. Artif. Int. Organs 17: 421 (1971)), artificial skin and blood vessels (Krajicek, M. et al. J. Surg. Res. 4. 290 (1964)), as hemostatic agents (U.S. Patent 4,215,200) , soft contact lens (U.S. Patents 4,264,155; 4,264,493; 4,349,470; 4,388,428; 4,452,925 and 4,650,616) and in surgery (Chvapil, M. et al. Int. Rev. Conn. Tiss. Res. 6: 1-61 (1973)).
  • Natural collagen fibers are basically insoluble in mature tissues because of covalent intermolecular crosslinks that convert collagen into an infinite crosslinked network. Disper ⁇ sal and solubilization of native collagen can be achieved by treatment with various proteolytic enzymes which disrupt the intermolecular bonds and removes immunogenic non-helical end regions without affecting the basic, rigid triple-helical structure which imparts the desired characteristics of collagen (see U.S. Patent Nos. 3,934,852; 3,121,049; 3,131,130; 3,314,8- 61; 3,530,037; 3,949,073; 4,233,360 and 4,488,911 for general methods for preparing purified soluble collagen) .
  • a biologi ⁇ cally compatible, collagenous reaction product with sealant and adhesive properties can be formed using chemically modified collagen. Modification of pure, soluble or partially fibrillar collagen monomers with an acylating agent or a sulfonating agent or a combination of the foregoing, renders collagen monomers soluble at physiological conditions. Subsequent polymerization of the chemically modified monomers produces a polymerized collagen composition with adhesive and sealant properties.
  • the polymerization reaction may be initiated with an appropriate poly erizion initiator such as a chemical oxidant, ultraviolet irradiation, a suitable oxidative enzyme or atmospheric oxygen.
  • polymerized chemically modified collagen composi ⁇ tions as a safe, effective biological adhesives with appropri ⁇ ate adhesive strength for biomedical applications, particularly involving soft tissues.
  • adhesives may be used to seal incisions following cataract removal and to attach epikeratoph- akic grafts to corneal tissue for correction of refractive errors.
  • the polymerized materials may assume a number of sizes and shapes consistent with their intended biomedical applications, which include use in ophthalmology, plastic surgery, orthopedics and cardiology.
  • FIGURES Figures la-c illustrates the attachment of a lent- icule by application of a collagen-based sealant at the periph ⁇ ery of the lenticule in epikeratoplastic procedures.
  • Figures 2a-c illustrates the attachment of a lentic ⁇ ule by application of a collagen-based sealant on top of the lenticule in epikeratoplastic procedures.
  • the applied col ⁇ lagen-based sealant coats and seals the lenticule in its entirety.
  • biologically compati ⁇ ble refers to collagen modified in accordance with the present invention (i.e., a polymerized collagenous reaction product) which is incorporated or implanted into or placed adjacent to the biological tissue of a subject and more particularly, does not deteriorate appreciably over time or induce an immune response or deleterious tissue reaction after such incorpora ⁇ tion or implantation or placement.
  • the type of collagen useful to form the biologically compatible collagenous reaction product with adhesive proper- ties of this invention is selected from the following groups: purified Type I collagen, Type IV collagen and Type III colla ⁇ gen, intact collagen-rich tissue or a combination of any of the foregoing.
  • Preferred as a collagen starting material is purified Type I collagen.
  • Type I collagen is ubiquitous and readily extracted from animal tissues such as dermis and tendon. Common sources are bovine tendon and hide and rat tail tendon. Extraction from human tissues is difficult.
  • U.S. patent No. 4,969,912, "Human Collagen Processing and Autoim- plant Use" describes unique methods to disperse and solubilize human tissue.
  • soluble collagen solutions useful for the instant invention A variety of collagen solubilization procedures that are well known in the art can be used to prepare soluble collagen solutions useful for the instant invention.
  • Native collagen is liberated from non-collagen connective tissue constituents (lipids, sugars, proteins, etc.) and isolated after subjecting it to proteolytic enzymatic treatment by an enzyme other than collagenase. Suitable proteolytic enzymes include pronase and pepsin.
  • the enzymatic treatment removes the immunogenic non-helical portions of native collagen (telo- peptide) and provides a monomeric collagen material which is soluble in dilute acidic aqueous media.
  • a solution containing crude solubilized collagen is then subjected to a series of treatments to purify the soluble atelopeptide collagen from insoluble collagen, protease and non-collagen products result- ing from the proteolytic enzymatic procedure.
  • Conventional methods for preparing pure, acid soluble, monomeric collagen solutions by dispersing and solubilizing native collagen are described, for example, in U.S. Patent Nos. 3,934,852; 3,121,049; 3,131,130; 3,314,861; 3,530,037; 3,949,073; 4,233,360 and 4,488,911.
  • a method for preparing a collagen solution is provided in the examples that follow.
  • Suitable acylating agents for use in the instant invention include aliphatic, alicyclic and aromatic anhydrides or acid halides.
  • Non-limiting examples of acylating agents include glutaric anhydride, succinic anhydride, lauric an ⁇ hydride, diglycolic anhydride, methylsuccinic anhydride, methyl glutaric anhydride, dimethyl glutaric anhydride, succinyl chloride, glutaryl chloride, and lauryl chloride. These chemicals are available from Aldrich Chemical Company (Mil- waukee, WI) .
  • Preferred acylating agent for use in the present invention is glutaryl anhydride.
  • an effective amount of an acylating agent is broadly from about 0.5 to 7.5% wt total collagen, preferably from about 1.5 to 5.0% total collagen in solution.
  • acylating agents having secondary reactive functionalities within their chemical structure are also useful for modifying collagen monomers. Examples of secondary functionalities include by way of non-limiting examples: epoxy, cyano, halo, alkenyl, and alkynyl.
  • Non- limiting examples of acylating agents bearing secondary func ⁇ tionalities include exo-3,6-epoxy-1,2,3,4-tetrahydrophthalic anhydride, methacrylic anhydride, 3,6-endoxo-3-methylhexahy- drophthalic anhydride, and endo-3,6-dimethyl-3,6-endoxohexa hydrophthalic anhydride.
  • Preferred as such acylating agents are exo-3,6-epoxy-1,2,3,4-tetrahydrophthalic anhydride and methacrylic anhydride.
  • the secondary functionalities present in acylating agents can react covalently with amino acid residues under acylation conditions or during polymerization.
  • Useful sulfonating agents for the preparation of modified collagen monomers of the present invention include aliphatic, alicyclic and aromatic sulfonic acids or sulfonyl halides.
  • Non-limiting examples of sulfonating agents for use in the present invention include anthraquinone-1, 5-disulfonic acid, 2- (chlorosulfonyl) -anthraquinone, 8-hydroxyquinoline sulfonic acid, 2-naphthalene- sulfonyl chloride, beta-styrene sulfonyl chloride and 2-acrylamido-2-methyl-l-propane sulfonic acid.
  • sulfonating agents for preparing the adhesive collagen materials are anthraquinone-1, 5-sulfonic acid and 2- (chlorosulfonyl) -anthraquinone.
  • Such compounds in non-toxic effective amounts, can be safely employed in collagen-based compounds for medical use as adhe ⁇ sives and sealants.
  • An effective amount of sulfonating agent is broadly from about 0.5 to 20% wt total collagen, preferably
  • the amount of acylating agent and sulfonating agent in total is preferably from about 1.5 to 7.5% wt of collagen in solution. Excess quantities of chemical modifiers beyond the preferred range may result in a collagen composition that is biologically unstable and sensitive to tissue proteases.
  • Acylation of collagen is carried out at alkaline pH, for example, in the range from about 7.5 to 10.0, preferably from about 8.5 to 9.5, and more preferably at about pH 9.0.
  • the acylation reaction can be monitored by the decrease in pH.
  • the reaction is complete when pH remains stable.
  • the reaction can also be monitored by removing aliquots and measuring the free amine concentration of precipitated, washed collagen product.
  • the acylation reaction should be complete in about 5 to about 90 minutes, preferably from about 20 to 40 minutes.
  • the reactions should be carried out at temperatures from about 4 C to 37*C, preferably from about 4 C to 25'C.
  • the reaction can be stopped by adjusting the pH to 12.0 for 2 minutes. This destroys residual, unreacted acyla ⁇ ting agent.
  • the modified collagen is then precipitated by reducing the pH using hydrochloric acid, acetic acid, nitric acid, sulfuric acid, or other acid.
  • the amount of acid must be sufficient to precipitate out the chemically derivatized collagen.
  • precipita ⁇ tion occurs at a pH of between about 3.5 and 6.0, preferably between about 4.0 and 5.0.
  • the precipitate of reacted collagen which now con ⁇ tains substituent groups reacted with amine groups (primarily epsilon-amino groups) , is recovered from the mixture using conventional techniques such as centrifugation or filtration. Centrifugation at about 3,000 to about 15,000 rpm for about 20 to 60 minutes, preferably from about 4,000 to 12,000 for about 20 to 30 minutes provides efficient recovery of the precipi ⁇ tate.
  • the precipitate is washed with deionized water and subsequently dissolved in a physiological solution, e.g., phosphate buffer (0.1 M) at pH 7.2. It is often necessary to adjust the pH from about 7.0 to 7.5 by addition of sodium hydroxide solution.
  • a physiological solution e.g., phosphate buffer (0.1 M) at pH 7.2. It is often necessary to adjust the pH from about 7.0 to 7.5 by addition of sodium hydroxide solution.
  • the solu ⁇ tion is generally filtered by conventional filtering means, i.e. a 5 micron filter, and then centrifuged to remove air bubbles.
  • filtering means i.e. a 5 micron filter
  • the resulting solution containing chemically modified collagen monomers exhibits a viscous consistency and varying degrees of transparency and clarity depending on the extent of acylation and on the state of solubility of the starting collagen material.
  • the extent of acylation determines the biological stability of the resultant sealant or adhesive structure. Complete acylation, reaction with all available free amines, produces a collagen composition with maximum amounts of adhe- sive moieties. However, such a material may not be biological ⁇ ly stable. Complete acylation results in a collagen sealant that rapidly degrades in the presence of neutral proteolytic enzymes, such as trypsin. It has been discovered that the biological stability of resultant sealants and adhesive systems can be manipulated by controlling the extent of acylation. The extent of acylation may be modulated by varying the amount of acylation agent, the pH, the temperature and the time of the reaction. In addition, the method of addition of the acylating agents will affect the reaction. Reactions are generally slower if the acylating agent is added as a solid or powder rather than as a solution.
  • SHEET adhesive that is resistant to neutral proteolytic enzymes. If the starting collagen solution is adjusted to pH 7.0-7.6 and allowed to undergo limited fibrillogenesis at 25 l to 37'C before chemical modification, the final sealant or adhesive complex is resistant to degradation by neutral proteolytic enzymes, such as trypsin.
  • the chemically modified collagen solution thus obtained is subsequently subjected to polymerization or cross- linking conditions to produce the polymerized collagen composi- tion of the present invention.
  • Polymerization may be carried out using irradiation, e.g., UV, gamma, or fluorescent light.
  • UV irradiation may be accomplished in the short wave length range using a standard 254nm source or using UV laser sources. With a standard 254nm source, 4-12 watts, polymerization occurs from 10 to 40 minutes, preferably 20 to 30 minutes, at an exposure distance of from 2.5-10 cm, preferably from 2.5 to 5 cm distance. Excess UV exposure will begin to depolymerize the collagen polymers.
  • Polymerization using gamma irradiation can be done using from 0.5 to 2.5 Mrads. Excess Gamma exposure will also depolymerize collage polymers. Polymerization in the presence of oxygen can be done by adding an initiator to the fluid prior to exposure.
  • initiators include sodiumpersulfate, sodium thiosulfate, ferrous chloride tetrahydrate, sodium bisulfite and oxidative enzymes such as peroxidase or catechol oxidase. When initiators are employed, polymerization occurs in 30 seconds to 5 minutes, usually from 1 to 3 minutes.
  • Preferred as a polymerizing agent is UV irradiation.
  • the polymerization or crosslinking of the monomeric substituents can be carried out by simply exposing the material to atmospheric oxygen, although the rate of polymerization is appreciably slower than in the case of UV irradiation or chemical agents.
  • SUBSTITUTESHEET acid may be mixed with N, N-methylene bisacrylamide to produce mechanical sealants and adhesive systems.
  • Addition of in ⁇ itiators such as sodium persulfate or ammonium persulfate, and exposure to fluorescent light rapidly results in polymerization to form polyacrylamide-collagen co-polymers.
  • Collagen products containing methacrylic acid polymerize spontaneously in air. This polymerization can be accelerated under UV irradiation in the absence of oxygen.
  • the polymerized collagenous reaction products can be made in the form of a sealant film.
  • a sealant film is flexible and elastic with the consistency and feel of plastic film, and yet the film exhibits high biological compatibility.
  • Uses of sealant films include: Prevention of adhesion formation following tendon surgery (i.e., use as a wrap around tendons), use as a syn ⁇ thetic tympanic membrane, substitute facial tissue and wound dressing component. Additional examples of potential usage of sealant films include: treatment of corneal abrasions, wound closure, coating of catheters and instruments, use as a materi ⁇ al to prevent adhesion formation in tissues other than tendons (e.g., peritoneal cavity).
  • the sealant and adhesive formulations can be used as systems specific for delivery of numerous drugs, growth factors, and biological compounds. Such materials can be added to the collagen adhesive or sealant to promote cell migration, cell adhesion, and wound healing.
  • Fibrous Type I collagen was prepared from bovine material (calf hide) using the following procedure:
  • SUBSTITUTESHEET Clean, dehaired split hides were purchased from the Andre Manufacturing Co. (Newark, N.J.) and frozen until ready for use. Approximately 200g of calf hide was thawed at room temperature and cut into approximately 1 cm 3 pieces using a scalpel and tweezers. The weight of the wet tissue was record ⁇ ed. The calf hide was then placed into 15 liters of 0.5M acetic acid and stirred with a lightening mixer at room temper ⁇ ature for at least one hour. A ten mL solution of 0.5M acetic acid containing 2% w/w (or 3.9g) pepsin from porcine mucosa (Sigma Chemicals, St.
  • Collagen was precipitated out by addition of solid NaCl to the supernatant to a final concentration of 2.5M. The solution was stirred at room temperature for at least two hours. The collagen precipitate was collected by centrifuga ⁇ tion of solution for 30 minutes at 9000 rpm and redissolved in 15 liters of 0.5M acetic acid, a process requiring at least 2 hours. Collagen was reprecipitated out again by addition of solid NaCl to the solution to a final concentration of 0.8M. The solution stirred for at least two hours and the collagen was collected by centrifugation of the solution for 30 minutes at 9000 rpm. This redissolving/precipitation procedure was repeated once more.
  • the final pellet, containing purified collagen was dissolved in 0.1M acetic acid of sufficient volume to provide approximately 0.3% w/w collagen Type I solution of pH 3.0.
  • the collagen solution was then prefiltered through a 0.3 micron filter and sterilized through a 0.22 micron filter.
  • the collagen solution can now be used in the modification process.
  • Pure collagen was prepared as previously described. Following filtration through a 0.2 micron filter, 100 ml of collagen solution was brought to pH 9.0 and reacted with 6.0 mg of 2- (chlorosulfonyl) -anthraquinone and then 6.0 mg of glutaric anhydride. These chemicals were added in solid form while maintaining the pH at 9.0. After 3 hours, the pH was reduced to 4.5 to precipitate the modified collagen. The precipitate was washed three times with deionized water and subsequently dissolved in 0.005M phosphate buffer, pH 7.5, containing 2% glycerol. The pH was adjusted to 7.4 using in sodium hydroxide. The material was slightly cloudy and was filtered through a 5 micron filter.
  • EXAMPLE 2 SEALING SYNTHETIC LENTICULES IN EPIKERATOPHAKIA
  • a 10 ul aliquot of sodium persulfate (20 mg/ml) was added to a solution containing collagen modified with glutaric anhydride alone.
  • the mixture was placed on the surface of an intact, enucleated bovine eye, and allowed to flow over the surface of the eye for about 2 minutes. At that point, the eye was exposed to UV irradiation for 30 seconds.
  • the collagen mixture polymerized into a thin, somewhat flexible film that covered the eye surface.
  • glutaric modified collagen without sodium persulfate was added to the surface of an intact, enucleated bovine eye.
  • the eye was then placed in an atmospheric chamber, the chamber flushed with nitrogen, and the eye with collagen coating exposed to UV irradiation for 20 minutes. Again, there appeared to be a smooth, very flexible film of collagen covering the eye.
  • Such a sealant could be useful for attaching a syn ⁇ thetic or natural lenticule in epikeratoplastic procedures.
  • the synthetic or natural lenticule would be posi ⁇ tioned on the corneal surface.
  • the collagen sealant would then be placed over the lenticule and adjacent corneal tissue and polymerized in place to seal the lenticule to the adjacent corneal tissue.
  • the collagen-based sealant can be applied on the periphery of the lenticule and adjacent corneal tissue ( Figure la) , then exposed to UV irradiation ( Figure lb) to seal the lenticule in place ( Figure lc) .
  • the collagen-based sealant can be placed on top of lenticule ( Figure 2a) which then flows over and coats the surface of the lenticule and adjacent corneal tissue. The coating is then exposed to UV irradiation ( Figure 2b) which seals the lenticule in place ( Figure 2c) .
  • Polymerization using UV irradiation must be accomplished in the absence of oxygen. Thus, formulations containing a safe initiator are more practical, eliminating the need to exclude oxygen.
  • pure, soluble collagen was prepared as previously described. Following filtration through a 0.2 um filter, the solution was brought to pH 7.0 and placed in a
  • the standard glutaric formulation was examined in situ by placing a sample of the material on the surface of a lenticule and then exposing the material to UV irradiation (short wave length) for 20 minutes in a nitrogen atmosphere.
  • the collagen material was formed into a thin solid film which covered the entire lenticule and seemed to provide a continuous tapering attachment to Bowman's membrane. Epithelial cell migration and attachment had started over the collagen film. However, some of the collagen film began to disintegrate before epithelial cell migration was complete. This probably was caused by epithelial cell proteases.
  • EXAMPLE 4 ADHESIVE FORMULATION Glutaric modified collagen was prepared using the procedures described in Example 3. The modified collagen was redissolved at about 5% concentration in phosphate buffer (0.005M at pH 7.5) containing 2% glycerol. This high con ⁇ centration material was supplemented with sodium persulfate (lOOul of a 20mg/ml solution) per 2 ml of redissolved collagen and used to join two sections of light cardboard. The fluid was painted onto the surfaces of the adjoining cardboard and allowed to wet the surfaces. The pieces were then exposed to UV irradiation for 2 minutes.
  • a collagen solution was obtained as previously described. After filtration through a 0.2 filter, 300 ml of collagen solution was brought to pH 7.5 and placed in a water bath at 37 l C until fibril formation was initiated. The pH of the solution was then raised to 9.0 and 42 mg of exo-3,6-epoxy- 1,2,3,4-tetrahydrophthalic anhydride added in 10 drops of dimethyl formamide. The pH was maintained at 9.0 for 30 minutes. After 30 minutes the pH was dropped to 7.5 and the solution allowed to equilibrate for an additional 30 minutes. The neutral solution was centrifuged at 9,000 rpm for 20 minutes, the supernatant removed and pH adjusted to 4.3 to precipitate the neutral soluble, epoxy-modified collagen.
  • the precipitate was washed three times with sterile water and reconstituted in 0.005M phosphate buffer, pH 8.6, containing 2% sterile glycerol. The resulting solution was clear, transpar ⁇ ent and viscous.
  • One aliquot of about 5 ml was removed and exposed to 254nm UV light for 5 minutes.
  • the material thick- ened but did not polymerize to a hard film.
  • Another aliquot of 5 ml was removed and 25 ul of sodium persulfate (20mg/ml) added. This was also exposed to 254 nm UV irradiation for 2 minutes.
  • the material polymerized to a relatively firm, but flexible film.
  • the modified collagen was then used to attach two sections of porous paper.
  • the bond was strong and required significant force to separate the two sections.
  • This same material was used to attach two sections of calf skin. UV irradiation in the absence of oxygen, was used as the initiator in place of the sodium persulfate. After 20 minutes, the sections were firmly attached.
  • soluble collagen 200 ml was modified at pH 9.0 with 30mg of methacrylic anhydride. The reaction continued for 30 minutes after which 10 mg of glutaric anhydride was added and reacted for another 30 minutes.
  • the modified collagen was precipitated by adjusting the pH to 4.5. The precipitate was recovered by centrifugation and washed three times with sterile water. The material was reconstituted in 0.005M phosphate buffer containing 2% glycerol. The solu ⁇ tion was clear and viscous. An aliquot was removed and exposed to 254nm UV irradiation. After 2 minutes, the material had formed a clear, firm film. Another aliquot was removed and placed on a microscope slide.
  • EXAMPLE 7 HUMAN TISSUE ADHESIVE MATERIAL
  • human dermis was dissected from full thickness skin specimen and blended using an OMNI homogenizer with a Macro generator (10mm) .
  • the tissue did not pulverize in buffer or saline.
  • To the tissue was added 5 mg of methacrylic anhydride per 200 mg of tissue.
  • the tissue immediately pulver- ized to a fine suspension.
  • a second aliquot of methacrylic anhydride was added to further solubilize the tissue.
  • the pulverized tissue was centrifuged to separate the soluble fraction from the dispersed fraction.
  • the modified tissue in the soluble fraction was recovered by adding 3 volumes of 70% ethanol.
  • the collagen immediately formed fibers.

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Abstract

Compositions à base de collagène utilisées comme adhésifs et agents d'étanchéité à usage médical, et leurs préparations. Avant polymérisation, on modifie chimiquement des monomères de collagène solubles ou partiellement fibrillaires en solution avec un agent d'acylation, un agent de sulfonation ou une combinaison de ceux-ci. Les compositions à base de collagène préparées selon l'invention peuvent être utilisées comme adhésifs à usage médical utilisés pour lier des tissus tendres, ou on peut leur donner la forme d'une couche mince d'étanchéité destinée à divers usages médicaux tels que des fermetures de plaies ainsi que des éléments enveloppant pour les tendons afin d'empêcher une adhésion post-chirurgicale.
PCT/US1992/000704 1991-01-29 1992-01-27 Adhesifs et agents d'etancheite a base de collagene et leurs procedes de preparation WO1992013025A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
DE69232835T DE69232835D1 (de) 1991-01-29 1992-01-27 Klebstoffe und dichtungsmasse auf basis von kollagen und verfahren zu deren herstellung
EP92907406A EP0569551B1 (fr) 1991-01-29 1992-01-27 Adhesifs et agents d'etancheite a base de collagene et leurs procedes de preparation
CA002101637A CA2101637C (fr) 1991-01-29 1992-01-27 Adhesifs et produits d'etancheite a base de collagenes et methode de preparation

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Application Number Priority Date Filing Date Title
US07/646,944 US5219895A (en) 1991-01-29 1991-01-29 Collagen-based adhesives and sealants and methods of preparation and use thereof
US646,944 1991-01-29

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DE (1) DE69232835D1 (fr)
WO (1) WO1992013025A1 (fr)

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EP0732109A1 (fr) * 1995-03-14 1996-09-18 Collagen Corporation Utilisation d'agents hydrophobes de réticulation pour préparer des compositions de biomatériaux réticulés
US7129209B2 (en) 1995-03-14 2006-10-31 Angiotech Pharmaceuticlas (Us), Inc. Use of hydrophobic crosslinking agents to prepare crosslinked biomaterial compositions
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US9579415B2 (en) 2006-02-14 2017-02-28 Cook Incorporated Joining and/or sealing tissues through photo-activated cross-linking of matrix proteins
US9669132B1 (en) 2006-02-14 2017-06-06 Cook Medical Technologies, LLC Joining and/or sealing tissues through photo-activated cross-linking of matrix proteins
US10441675B2 (en) 2006-02-14 2019-10-15 Cook Medical Technologies Llc Joining and/or sealing tissues through photo-activated cross-linking of matrix proteins
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Publication number Publication date
US5219895A (en) 1993-06-15
US5874537A (en) 1999-02-23
DE69232835D1 (de) 2002-12-05
CA2101637A1 (fr) 1992-07-30
EP0569551A1 (fr) 1993-11-18
CA2101637C (fr) 2003-08-19
US5354336A (en) 1994-10-11
EP0569551B1 (fr) 2002-10-30
EP0569551A4 (fr) 1995-06-14

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